Classifications

• • C—CHEMISTRY; METALLURGY
  • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
  • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
  • C08L53/00—Compositions of block copolymers containing at least one sequence of a polymer obtained by reactions only involving carbon-to-carbon unsaturated bonds; Compositions of derivatives of such polymers
• • C—CHEMISTRY; METALLURGY
  • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
  • C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
  • C08L53/00—Compositions of block copolymers containing at least one sequence of a polymer obtained by reactions only involving carbon-to-carbon unsaturated bonds; Compositions of derivatives of such polymers
  • C08L53/005—Modified block copolymers
• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
  • A61K9/00—Medicinal preparations characterised by special physical form
  • A61K9/0012—Galenical forms characterised by the site of application
  • A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
  • A61K9/0024—Solid, semi-solid or solidifying implants, which are implanted or injected in body tissue

Definitions

• the present invention relates to a stereo photo hydrogel, to a process of making stereo photo hydrogels, to polymers for use in making such hydrogels and a pharmaceutical kit comprising such polymers.
• Hydrogels have been widely used for biomedical applications, such as tissue engineering and drug delivery, due to their favorable characteristics.
• 1"3 Hydrogels are water-swollen networks of crosslinked hydrophilic polymers. Their high water content renders them highly biocompatible and also leads to minimal adsorption of proteins.
• the mechanical properties of hydrogels parallel those of soft tissues, making them particularly interesting for tissue engineering.
• Hydrogels may be formed in situ, thus allowing easy mixing of cells and bioactive molecules, such as proteins, with the polymer solutions prior to gelation.
• 4"6 Moreover, in situ hydrogel formation enables the preparation of complex shapes and use of minimally invasive surgery. In situ forming hydrogels have been prepared by physical and chemical crosslinking methods.
• Physically crosslinked hydrogels include those based on hydrophobic interactions and hydrogen bonds between thermosensitive block or graft polymers 7"11 , stereocomplexation between poly(L-lactide) (PLLA) and poly(D-lactide) (PDLA) graft 12 and block copolymers 13"15 , inclusion complexation using ⁇ -dextrin polymers 16"20 , and ionic interactions between oppositely charged microparticles 21 or peptides 22 .
• the crosslinking conditions for these gels are generally very mild, thus allowing the entrapment of labile compounds, such as proteins. However, in general they are mechanically weak compared to chemically crosslinked hydrogels and changes in the external environment (e.g.
• Chemically crosslinked hydrogels have been formed in situ by Michael addition between thiols and acrylates or vinyl sulfones 23 29 , reaction between aldehydes and dihydrazides 30 or amines 31 , reaction between activated esters and amines 32 and redox initiated radical chain polymerization of (meth)acrylates 33 37 .
• Photopolymerization of (meth)acrylates 5 using UV-light 38" 41 or visible light 42"44 has been mostly used for in situ formation of chemically crosslinked hydrogels.
• Biodegradable hydrogels prepared by photocrosslinking of poly(ethylene glycol)-poly(lactide) (PEG-PLA) diacrylate derivatives were first reported by the group of Hubbell. 42 More recently, this group has prepared degradable hydrogels by the incorporation of plasmin degradable peptide sequences. 39 ' 43 When modified with cell-adhesive RGD peptide sequences, these hydrogels supported three-dimensional outgrowth of human fibroblasts embedded as a cluster within the hydrogel. Another type of degradable hydrogel was prepared by copolymerization of a hyaluronic acid methacrylate derivative and PEG diacrylate. 44 Fibroblasts adhered and proliferated when cultured on the RGD functionalized hydrogels.
• the group of Anseth has done much work on degradable hydrogels based on PEG-PLA dimethacrylates. 40 It was shown that by using combinations of PEG and PEG- PLA dimethacrylates and/or by changing the PLA block length, the hydrogel degradation rate, compressive modulus and crosslinking density could be tuned to provide suitable scaffolds for cartilage tissue engineering. 41
• the major advantage of photopolymerization is the spatial and temporal control over the polymerization. However, photopolymerization in vivo is hampered by the absorption of UV-light by the skin (> 99%). In clinical applications, fast gelation is desired to prevent diffusion of hydrogel precursors or bioactive molecules to the surrounding tissue. Elisseeff et al.
• the remaining unsaturated bonds may cause toxicity problems and incomplete conversion may result in hydrogels with weak mechanical properties.
• the polymerization rate may be increased by increasing the photoinitiator concentration or the intensity of the incident light. However, due to their toxicity photoinitiators can only be used at low concentrations (ca. 0.01-0.05 wt%) 49 and the intensity of the UV-light is limited to ca. 5-10 mW/cm 2 to prevent cell damage. Visible light is less attenuated by the skin, but efficient initiators with less cytotoxicity are required. 49 ' 50 Another problem of photopolymerization is that fast polymerization is generally accompanied by substantial heat effects. 48 The resulting temperature rise may cause local cell morbidity and tissue necrosis surrounding the implant.
• the present invention has for its object to provide a hydrogel which is fast in situ forming and is robust.
• the present invention is based on the insight that by the combined use of stereo complexation and photo polymerization gelation will be fast and photo polymerization will be facilitated.
• After rapid formation of the stereo complexed hydrogel subsequent photo polymerization can be carried out at a relatively low polymerization rate to provide gels with the desired mechanical properties.
• the local temperature rise by heat generated by the photo polymerization will be limited.
• the photo polymerization may take place at lower initiator concentrations and at lower irradiation intensity as compared to gel formation without using preformed stereo complexes.
• the stereo photo hydrogel formed will have increased mechanical properties and if desired prolonged degradation times.
• the stereo complexation aids in the photo polymerization of the photo cross-linkable component.
• the stereo photo hydrogels formed will have increased storage moduli and if desired improved degradation times in comparison to photo hydrogels formed by photo polymerization only.
• the present invention provides stereo photo hydrogels formed by stereo complexed and photo cross-linked polymers, which polymers comprise at least two types of polymers having at least one hydrophilic component, at least one hydrophobic mutually stereo complexing component, and at least one of the types comprises at least one photo cross-linkable component. Accordingly, this stereo photo hydrogel is formed by stereo complexed and photo cross-linked polymers.
• These polymers comprise at least two types of polymers.
• the polymers of both types have at least one hydrophilic component required for forming the hydrogel.
• the polymers further comprise at least one hydrophobic stereo complexing component which will mutually stereo complex thereby forming the stereo hydrogel.
• At least one of the two types of polymers comprises at least one photo cross-linkable component.
• the polymers of at least one of the two types are cross-linked by photo polymerization thereby forming the stereo photo hydrogel.
• the two types of polymers comprise at least one mutually photo cross-linkable component. Accordingly, both types of polymers are mutually photo cross-linked such that both types of polymers are covalently bound thereby forming a very robust stereo-photo hydrogel.
• hydrophilic component for each of the two types of polymers examples include PEG, dextran, hyaluronic acid, pullulan, chondroitin sulfate, poly (vinyl alcohol), poly(hydroxyethyl methacrylate), poly(aspartic acid), poly (glutamic acid), poly(acrylic acid), and poly((C1-C6)alkyloxazoline), such as poly(methyl- or ethyl-oxazoline).
• PEG having a number average molecular weight of for instance 10.000-50.000, such as 20-30.000.
• hydrophobic stereo complexing component comprises poly (L-lactide) or poly (D-lactide).
• each poly(L-lactide) or poly (D-lactide) could comprise 3-30 lactyl units per poly. (L- or D-lactide). More preferably the number of lactyl units per poly (L- or D-lactide) is 10-20, more preferably 12-16. This depends on the hydrophobic character required for the stereo complexing component relative to the hydrophilic character of the hydrophilic component and the character of the photo cross-linkable component.
• the photo cross-linkable component may comprise acrylate, methacrylate, acrylamide and fumarate.
• Preferred as a photo cross-linkable components are acrylate and methacrylate.
• the photo cross-linkable component may be cross-linked using visible or ultraviolet irradiation, depending on the use.
• visible or ultraviolet irradiation For the in-vivo formation of the stereo-photo hydrogel it is preferred to use long wavelength ultraviolet irradiation.
• long wavelength ultraviolet irradiation the intensity of the UV irradiation may be relatively low.
• photo crosslinking may be carried out at lower rates.
• the UV irradiation may be as low as 0.05-20 mW/cm 2 (when there is a tissue barrier (such as intact skin) or from 2-20 mW/cm 2 when there is no tissue barrier.
• the intensity of the visible light is preferred from 30-100 mW/cm 2 .
• the two types of polymers may have the same or mutually different structures.
• the stereo complexing component and the photo cross-linkable component are both directly linked to the hydrophilic component.
• the photo cross-linkable component is linked to the stereo complexing component which in turn is linked to the hydrophilic component.
• hydrogels may be formed, in which the constituting polymers have the form of a triblock or the form of a multi arm structure.
• the number of arms is preferably between 3-12, more preferably between 8-10 arm structures.
• the hydrogels according to the invention have advantageous properties.
• One of the advantageous properties of the hydrogel is a storage modules G' larger than IkPa. Storage moduli G' up to 15OkPa may be obtained. Accordingly, the hydrogels may have a storage modules G' within the range of about 1-15OkPa, preferably within the range of 1-10OkPa.
• Another aspect of the present invention relates to the process of making the stereo-photo hydrogels according to the invention. Based on the insight of the present invention the stereo-photo hydrogel is formed by first stereo complexing two types of polymers (as described above). Subsequently, the formed stereo complexed hydrogel is subjected to photo cross-linking thereby forming the stereo-photo hydrogel.
• the present invention provides a process of making stereo photo hydrogel comprising the steps of a. providing a mixture of at least two types of polymers having at least one hydrophilic component, at least one hydrophobic mutually stereo complexing component and at least one of the types comprises at least one photo cross-linkable component; b. stereo complexing the two types of polymers, thereby forming a stereo complexed hydrogel; and c. photo cross-linking the stereo complexed hydrogel using visible or
• the two types of polymers are mixed which will, dependent on the circumstances, result in the stereo complexing of both types of polymers within a given time period. In this time period the stereo complexed hydrogel is formed. Subsequently, the stereo complexed hydrogel is subjected to photo cross-linking using irradiation thereby forming the stereo-photo hydrogel.
• the irradiation may be (low intensity) UV irradiation or visible light.
• the two types of polymers both comprise a photo cross-linkable component. Accordingly, both types of polymers are photo cross-linked resulting in a robust stereo photo hydrogel.
• the photo cross-linking may be carried out in the presence of a photo initiator.
• a photo initiator preferably in an amount of 0.001 to 0.05 wt%).
• Suitable examples are 2.2- dimethoxy-2-phenylacetophenone (Irgacure 65I), 1-hydroxycyclohexyl phenyl ketone (Irgacure 184), 2-methyl-1-[4-(methylthio) phenyl]-2-(4-morpholinyl)-1- propanone (Irgacure 907), and 2-hydroxy-1-(hydroxyethoxy)phenyl]-2methyl- 1-propanone (Darocur 2959), camphorquinone (CQ) with ethyl 4-N,N- dimethylaminobenzoate (4EDMAB) and triethanolamine (TEA) and the photosensitizer isopropyl thioxanthone.
• Irgacure 65I 1-hydroxycyclohexyl phenyl ketone
• the mixture of the two types of polymers may comprise the polymers in any suitable concentration for subsequent stereo complexing.
• the polymer concentration is within the range of 5-30wt-v%.
• the polymer concentration is within the range of 10-20wt-v%.
• Dependent on the type of polymers, their structure and the concentration the stereo complexing time is within the range of 1 minute-3 days. Accordingly, it is possible in relation to the objective use of the photo stereo hydrogels to select the time of stereo complexing as required.
• short or relatively short times for stereo complexing may be selected when it is desired to include within the stereo complexed hydrogel and subsequently within the stereo-photo hydrogel a component which may leach out or may be diffused out of the stereo photo hydrogel over an extended period of time and not during the stage of forming the stereo complex and the formation of the stereo-photo hydrogel. Then relatively short times for stereo complexing may be selected.
• the time for stereo complexing is within 2 hours to 1 day, and more preferably within 4-10 hours.
• the stereo-photo hydrogels will be subject to hydrolysis and thereby degradation of the hydrogel. Hydrolysis preferably takes place by hydrolysis of the hydrophobic component and more preferably by hydrolysis of the poly- lactide chain.
• the stereo-photo hydrogel When the stereo-photo hydrogel is formed of polymers having structures in which the photo cross-linkable component is at the end of some or all hydrophobic components, then degradation will result in a clear solution within a period of time of about 1 day-7 weeks, such as 1-3 weeks. If the stereo-photo hydrogel is formed by structures in which the hydrophobic component and the photo cross-linkable component are both directly linked to the hydrophilic component, then degradation by hydrolysis of the hydrophobic component will result in a swollen hydrogel which will subsequently degrade by hydrolysis of the photo cross-linkable component and then form a clear solution. Degradation from the swollen hydrogel into the clear solution will take 2-30 weeks, such as 5-25 weeks, more preferably 7-21 weeks. Clearly, the swollen hydrogel has different properties than the stereo- photo hydrogels.
• the hydrogels may comprise a pharmaceutically active agent or a moiety that binds a pharmaceutically active agent.
• Pharmaceutically active agents may be any pharmaceutically active compound used for therapy, diagnosis or prophylaxis of a human or animal body.
• the pharmaceutically active agent may comprise cells and biologically active molecules such as proteins, antibodies and the like.
• Another aspect of the present invention relates to the polymers of both types as discussed above. Both types of polymers are suitable for use in making a hydrogel which may comprise a pharmaceutical active agent or moiety that binds a pharmaceutically active agent.
• Such hydrogel may have the form of a medicament for the treatment of the human or animal body. The treatment is related to the biological activity of the pharmaceutically active agent as discussed above.
• the present invention relates to a pharmaceutical kit which may be used for in-situ or in-vitro forming of a stereo-photo hydrogel according to the present invention.
• Such pharmaceutical kit comprises two containers each comprising one of two types of polymers having at least one hydrophilic component, at least one hydrophobic mutually stereo complexing component, and at least one of the types comprises at least one photo cross-linkable component.
• the stereo-photo hydrogel is to comprise the pharmaceutically active agent or a moiety binding a pharmaceutically active agent, then it is preferred that the pharmaceutically active agent is contained in one or both containers for each of the two types of polymers. If possible or needed, the pharmaceutically active agent or the moiety that binds a pharmaceutically active agent is present in a separate container. Prior to the formation of the stereo hydrogel and the stereo-photo hydrogel, the content of one or more containers is mixed.
• figure 2 shows the storage modulus (G') and loss modulus (G") of stereo hydrogels containing equimolar amounts of PEG-PLLA 12 and PEG- PDLA 12 , PEG-PLLA 12 -MA and PEG-PDLA 12 -MA, or PEG-MA/PLLA 12 and PEG-MA/PDLA 12 star block copolymers in HEPES buffered saline (pH 7) at 37 0 C.
• G' storage modulus
• G" loss modulus
• L-lactide and D-lactide were obtained from Purac and recrystallized from dry toluene.
• the single site Zn-complex catalyst
• PEG-PLLA 12 -MA and PEG-PDLA 12 -MA were synthesized by partial methacrylation of the hydroxyl groups of PEG-PLLA 12 and PEG-PDLA 12 , respectively, according to the procedure reported by Lin-Gibson et al. 54 Typically, PEG-PLLA 12 (5.0 g, 0.174 mmol, dried overnight under vacuum over phosphorous pentoxide) was dissolved in 18 ml of DCM. A solution of TEA (0.171 g, 1.690 mmol) in 1 ml of DCM was added and the reaction mixture was cooled in an ice bath.
• TEA 0.171 g, 1.690 mmol
• PEG-MA For the synthesis of PEG-MA, typically, PEG (16.0 g, 0.734 mmol) was dissolved in 33 ml of DCM. A solution of TEA (0.442 g, 4.368 mmol) in 1 ml of DCM was added and the reaction mixture was cooled in an ice bath.
• PEG-MA/PLLA and PEG-MA/PDLA were synthesized by ring opening polymerization of L-lactide and D-lactide, respectively, in DCM at room temperature, initiated by the remaining hydroxyl groups of PEG-MA (dried overnight under vacuum over phosphorous pentoxide).
• the single site Zn- complex Zn(Et)[OC 6 H 3 (CH 2 Me 2 )-2-Me-4] was used as a catalyst.
• the number of lactyl units per PLA block was calculated based on the methyl protons of lactyl units ( ⁇ 1.4-1.5) and the methylene protons of PEG ( ⁇ 3.6).
• the number of methacrylate groups per PEG molecule was determined based on the methylene protons of PEG ( ⁇ 3.6) and the methylene protons of the methacrylate group ( ⁇ 5.6 and 6.2).
• CGCs Critical gel concentrations
• Both PEG-PLA-MA or PEG-MA/PLA stereocomplexed hydrogels and solutions of PEG-PLLA-MA or PEG-MA/PLLA single enantiomers in HEPES buffered saline were UV-irradiated and at the same time measured at 37 0 C. lrgacure 2959 was used as photoinitiator at a concentration of 1-5 mol% relative to the methacrylate groups.
• the stereo hydrogels were measured 10 min after mixing the enantiomeric solutions, unless mentioned otherwise.
• Hydrogels for scanning electron microscopy (SEM) experiments and swelling/degradation tests were prepared similarly in a 96 wells plate with sample volumes of 125 ⁇ l, resulting in cylinders of ca. 4 mm in height and 6 mm in diameter.
• PEG-PLA 12 -MA or PEG-PUWMA stereo-photo hydrogels were prepared by UVA-irradiation (250 mW/cm 2 ) for 10 min of the stereo hydrogels (equilibrated for ca. 15 min after mixing of the enantiomeric solutions) with 8 mol% initiator concentration (with respect to the methacrylate groups) prepared in HEPES buffered saline.
• Photo hydrogels were formed similarly by UVA-irradiation of PEG-PLLAi 2 -MA or PEG-MA 16 /PLLA single enantiomer solutions in HEPES buffered saline.
• the hydrogel cylinders were placed in vials and after addition of 1 ml of HEPES buffered saline the hydrogels were allowed to swell at 37 °C.
• the swelling experiment was performed in duplicate or triplicate.
• the swollen hydrogels were weighed at regular intervals after removal of the buffer. After each weighing the buffer was refreshed.
• the swelling ratio of the hydrogels was calculated from the initial hydrogel weight after hydrogel preparation (UVb) and the swollen hydrogel weight after exposure to buffer (W t ):
• PEG-PLA methacrylate functionalized poly(ethylene glycol)- poly(lactide) star block copolymers
• PEG-poly(L-lactide)- methacrylate PEG-PLLA-MA
• PEG-poly(D-lactide)-methacrylate PEG- PDLA-MA
• PEG-MA/PLLA ⁇ oly(ethylene glycol)-methacrylate/poly(D-lactide)
• PEG- MA/PDLA ⁇ oly(ethylene glycol)-methacrylate/poly(D-lactide)
• the PLA hydroxyl end groups were reacted with methacrylic anhydride using triethylamine (TEA) as a catalyst and dichloromethane (DCM) as a solvent at 30 0 C.
• TAA triethylamine
• DCM dichloromethane
• the PEG- PLLA 12 -MA and PEG-PDLA 12 -MA copolymers were recovered by precipitation in a diethyl ether/hexane/methanol mixture (10/1/1 v/v) (Table 1 , entry 3 and 4).
• 1 H NMR showed a degree of methacrylation of ca. 40%, determined by comparing the integrals of the peaks corresponding to the methylene protons of the methacrylate group ( ⁇ 5.6 and 6.2) and the methylene protons of PEG ( ⁇ 3.6).
• DCM dichloromethane
• PEG-MA/PLA copolymers with 12 and 16 lactyi units per PLA block were prepared by varying the feeding ratio of lactide to PEG (Table 1 , entry 5-8).
• the use of the single site Zn- catalyst allowed excellent control over the degree of polymerization of the PLA blocks and the methacrylation reaction was reproducible, giving similar degrees of methacrylation (Table 1).
• PEG-PLLAi 2 -MA single enantiomer The CGC of PEG-PLLAi 2 -MA single enantiomer is somewhat lower compared to PEG-PLLAi 2 single enantiomer, which is attributed to the increased hydrophobicity of PEG-PLLAi 2 -MA.
• Aqueous solutions of PEG-MA/PLLAi 2 single enantiomer could be prepared up to much higher polymer concentrations compared to PEG-PLLAi 2 -MA single enantiomer.
• Stereo hydrogels could also be formed from PEG-MA/PLLA 12 and
• PEG-MA/PDLA12 copolymers but at much higher polymer concentrations compared to PEG-PLLA 12 -MA and PEG-PDLAi 2 -MA copolymers.
• the higher CGC for stereocomplexation of PEG-MA/PLA 12 compared to PEG-PLA 12 -MA is due to the lower crosslinking functionality (i.e. number of PLA blocks per molecule) and lower hydrophobicity of PEG-MA/PLA 12 compared to PEG- PLA 12 -MA.
• the CGC for stereocomplexation of PLA-PEG-PLA triblock copolymers are higher compared to the CGC of eight- arm PEG-PLA star block copolymers.
• 13 PEG-MA/PLA 16 copolymers showed lower CGC values for stereocomplexation compared to PEG-MA/PLA 12 copolymers, due to the increased PLA block length.
• Stereo hydrogels were prepared by mixing aqueous solutions of equimolar amounts of PEG-PLLA 12 and PEG-PDLA 12 , PEG-PLLA 12 -MA and PEG-PDLA 12 -MA, or PEG-MA/PLLA 12 and PEG- MA/PDLAi 2 star block copolymers in HEPES buffered saline (pH 7) in a polymer concentration range of 12.5 to 17.5 w/v%. After mixing, the solutions were quickly applied to the rheometer and the evolutions of the storage modulus (G') and loss modulus (G”) were recorded (Figure 2a).
• HEPES buffered saline pH 7
• Figure 2a shows that the storage modulus evolutions and plateau values of PEG-PLA 12 -MA and PEG-PLA 12 copolymers were similar, which agrees well with the vial tilting tests, indicating that the methacrylate groups hardly influence the stereocomplexation (Table 2).
• Table 2a For PEG-PLA 12 and PEG-PLA 12 -MA copolymers the storage modulus plateau value was reached within ca. 5 h after mixing ( Figure 2a).
• the storage moduli of PEG-MA/PLA 16 stereo hydrogels continuously increased over 48 h.
• the storage moduli of the stereo hydrogels increased from 2.4 to 12.5 kPa for PEG-PLA 12 -MA and from 0.1 to 5.2 kPa for PEG-MA/PLA 16 , upon increasing the polymer concentration from 12.5 to 15 w/v% ( Figure 2b).
• Figure 3 shows that the gelation time of PEG-PLLAi 2 -MA single enantiomer at 15 w/v% polymer concentration decreased rapidly with increasing initiator concentration.
• the gelation times of PEG-PLLAi 2 - MA single enantiomer were 6.5 and 1.7 min, respectively.
• the 15 w/v% PEG-PLLAi 2 -MA single enantiomer solution did not form a gel within 15 min ( Figure 3b).
• a stereo hydrogel was formed within 1-2 min after mixing aqueous solutions of equimolar amounts of PEG-PLLAi 2 -MA and PEG- PDLAi 2 -MA copolymers.
• UV-irradiation of the stereo hydrogel at 1 mol% initiator and 15 w/v% polymer concentration 10 min after mixing increased the storage modulus from 5.6 to 9.6 kPa within 15 min due to photocrosslinking (Figure 4a).
• an initiator concentration of 1 mol% corresponds to 0.003 wt%, which is very low compared to the commonly used concentration of 0.05 wt%. 49 Low initiator concentrations are preferred, due to toxicity of the initiator.
• the photocrosslinking at this low initiator concentration implies in turn that low light intensities may be used to obtain stereo-photo hydrogels.
• the storage modulus of the stereo-photo hydrogel is highly dependent on the stereocomplex equilibration time before UV-irradiation.
• Figure 4b shows a plot of the ratio of the storage modulus of a PEG-PLAi 2 -MA stereo-photo hydrogel and the storage modulus plateau value of the corresponding stereo hydrogel (reached after ca. 5h, Figure 2a) as a function of the stereocomplex equilibration time.
• the storage modulus plateau value of the stereo-photo hydrogel (after 8 min of UV-irradiation) increased linearly with increasing the stereocomplex equilibration time at 15 w/v% polymer concentration and 5 mol% initiator concentration (corresponding to 0.015 wt%).
• This initiator concentration is low compared to the generally used concentration of 0.05 wt%.
• 49 UV-irradiation after 6 h of equilibration resulted in an almost 6-fold increase in the storage modulus of the PEG-PLAi 2 -MA stereo-photo hydrogel compared to the corresponding PEG-PLA 12 -MA stereo hydrogel (31.6 vs. 5.6 kPa) and a 17-fold increase compared to the corresponding PEG-PLLA 12 -MA photo hydrogel and (31.6 vs. 1.8 kPa). Since the hydrophobic methacrylate groups are at the PLA chain ends, the chemical crosslinks are most probably formed in the PLA domains.
• FIG. 5 A schematic representation of the stereo and stereo-photo hydrogel preparation for PEG-PLA-MA and PEG-MA/PLA copolymers is shown in Figure 5.
• the photoinitiator used lrgacure 2959
• lrgacure 2959 is rather hydrophobic (maximum concentration in water is 0.7 wt% 49 ), and may therefore preferably partition into the hydrophobic PLA domains, thereby increasing the local initiator concentration and thus photopolymerization rate in these domains. Therefore, the increased storage modulus upon increased stereocomplex equilibration time may be due to the formation of more PLA domains, resulting in a more densely crosslinked network and increased photopolymerization conversion.
• PEG-MA/PLA 16 stereo-photo hydrogels also showed much higher storage moduli compared to the corresponding PEG-MA/PLLA 16 stereo or photo hydrogels (results not shown). Therefore, combining stereocomplexation and photocrosslinking may provide fast gelation in vitro and in vivo 55 , yielding hydrogels with good mechanical properties.
• stereo-photo and photo hydrogels were prepared by UVA-irradiation (250 mW/cm 2 ) of PEG-PLA 12 -MA or PEG-MA/PLA 16 stereo hydrogels (equilibrated for ca.
• FIG. 6A and 6B show that PEG-PLA 12 -MA stereo-photo hydrogels have pore sizes of ca. 5 ⁇ m, while PEG-PLLA 12 -MA photo hydrogels have pore sizes of ca. 10 ⁇ m, indicating that stereocomplexation has a significant influence on the pore size of the freeze-dried PEG-PLA-MA hydrogels.
• freeze dried PEG- MA/PLA 16 stereo-photo hydrogels and PEG-MA/PLLA 16 photo hydrogels showed similar pore sizes (ca. 10 ⁇ m, Figure 6C and 6D).
• the position of the crosslinking group has much influence on the pore size of freeze-dried stereo-photo hydrogels.
• Hydrogels based on PEG-PLA-MA or PEG-MA/PLA copolymers were degradable under physiological conditions.
• stereo-photo and photo hydrogels were prepared by UVA-irradiation (250 mW/cm 2 ) of PEG-PLA 12 -MA or PEG-MA/PLA 16 stereo hydrogels (equilibrated for ca. 15 min after mixing the enantiomeric solutions) and solutions containing PEG-PLLAi 2 -MA or PEG-MA/PLLA 16 single enantiomer, respectively, in HEPES buffered saline (pH 7) at 8 mol% initiator concentration.
• the swelling ratio remained constant for the PEG-PLA 12 -MA stereo-photo hydrogels, while the swelling ratio of PEG-PLLA 12 -MA photo hydrogels continued to increase.
• both hydrogels disintegrated, as shown by the decreasing swelling ratio, until they finally dissolved completely.
• the degradation time is defined as the time required to completely dissolve at least one of the two or three hydrogels used for testing one type of hydrogel.
• Figure 7a shows that the PEG-PLA 12 -MA stereo-photo hydrogels were completely degraded after ca. 3 weeks and increasing the polymer concentration from 12.5 to 17.5 w/v% hardly affected the degradation time.
• the degradation time of the PEG-PLAi 2 -MA stereo hydrogels was twice as high as compared to the PEG-PLLAi 2 -MA photo hydrogels (ca. 3 vs. 1.5 weeks, Figure 7a). This may be due to a higher crosslinking density of PEG-PLAi 2 -MA stereo-photo hydrogels compared to PEG-PLLAi 2 -MA photo hydrogels, as was also shown by the rheology measurements.
• the PEG- MA/PLA1 6 stereo-photo hydrogels swelled over a period of ca. 5 weeks until reaching ca. twice their initial weight, independent of the polymer concentration (Figure 7b).
• PEG-MA/PLA stereo-photo hydrogels leads to the formation of a less densely, chemically crosslinked network with increased swelling ( Figure 8).
• the swollen PEG-MA/PLA stereo-photo hydrogels finally degrade through hydrolysis of the ester bonds of the polymerized methacrylate groups. It is possible to combine PEG-PLA-MA and PEG-MA/PLA copolymers to vary the degradation time.
• PEG-PLA-MA copolymers were prepared by methacrylation of ca. 40% of the PLA hydroxyl end groups of eight-arm PEG-PLA star block copolymers.
• PEG-MA/PLA copolymers were prepared by ring opening polymerization of lactide initiated by eight-arm star PEG with 40% of its hydroxyl end groups methacrylated.
• PEG-PLA-MA and PEG-MA/PLA stereocomplexed hydrogels could be rapidly formed in situ upon mixing aqueous solutions containing equimolar amounts of PEG-PLLA-MA and PEG-PDLA-MA, or PEG-MA/PLLA and PEG-MA/PDLA copolymers.
• stereocomplexation aided in the photopolymerization of the methacrylate groups.
• Photocrosslinking of stereo hydrogels yielding stereo-photo hydrogels, resulted in increased hydrogel storage moduli, compared to the hydrogels crosslinked by only stereocomplexation (stereo hydrogels) or only photocrosslinking (photo hydrogels).
• photocrosslinking of stereo hydrogels already took place at very low initiator concentrations.
• the degradation time of PEG-PLA- MA stereo-photo hydrogels was doubled compared to PEG-PLLA-MA photo hydrogels (ca. 3 vs. 1.5 weeks).
• PEG-MA/PLA stereo-photo hydrogels degraded within ca. 7 to over 16 weeks, depending on the polymer concentration.
• PEG-PLA-MA and PEG-MA/PLA may be combined to vary the hydrogel degradation rate.
• the fast gelation in vitro and in vivo due to stereocomplexation circumvents the need for fast photopolymerization, thus preventing substantial heat effects due to the photopolymerization and potentiating the use of low initiator concentrations and low light intensities.
• the fast gelation allows for easy handling.
• stereo-photo hydrogels and in particular the process for their formation in situ within the human or animal body will have a high potential for in vivo applications including tissue engineering and drug delivery.

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• 2007
  • 2007-03-20 DK DK07711990.7T patent/DK2147031T3/da active
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  • 2007-03-20 PT PT07711990T patent/PT2147031E/pt unknown
  • 2007-03-20 EP EP07711990A patent/EP2147031B1/en not_active Not-in-force
  • 2007-03-20 ES ES07711990T patent/ES2378838T3/es active Active
  • 2007-03-20 AT AT07711990T patent/ATE524504T1/de active
• 2011
  • 2011-12-12 CY CY20111101228T patent/CY1112131T1/el unknown

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